EP0201529A1 - Systeme humidificateur d'air destine a la respiration. - Google Patents

Systeme humidificateur d'air destine a la respiration.

Info

Publication number
EP0201529A1
EP0201529A1 EP85905291A EP85905291A EP0201529A1 EP 0201529 A1 EP0201529 A1 EP 0201529A1 EP 85905291 A EP85905291 A EP 85905291A EP 85905291 A EP85905291 A EP 85905291A EP 0201529 A1 EP0201529 A1 EP 0201529A1
Authority
EP
European Patent Office
Prior art keywords
air
temperature
humidifier
water
heater
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Granted
Application number
EP85905291A
Other languages
German (de)
English (en)
Other versions
EP0201529B1 (fr
Inventor
Harold U Bartels
Finn Sveen
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Bird Products Corp
Original Assignee
Bear Medical Systems Inc
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Bear Medical Systems Inc filed Critical Bear Medical Systems Inc
Publication of EP0201529A1 publication Critical patent/EP0201529A1/fr
Application granted granted Critical
Publication of EP0201529B1 publication Critical patent/EP0201529B1/fr
Anticipated expiration legal-status Critical
Expired - Lifetime legal-status Critical Current

Links

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
    • A61M16/10—Preparation of respiratory gases or vapours
    • A61M16/14—Preparation of respiratory gases or vapours by mixing different fluids, one of them being in a liquid phase
    • A61M16/16—Devices to humidify the respiration air
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
    • A61M16/08—Bellows; Connecting tubes ; Water traps; Patient circuits
    • A61M16/0816—Joints or connectors
    • A61M16/0841—Joints or connectors for sampling
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
    • A61M16/10—Preparation of respiratory gases or vapours
    • A61M16/1075—Preparation of respiratory gases or vapours by influencing the temperature
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
    • A61M16/10—Preparation of respiratory gases or vapours
    • A61M16/1075—Preparation of respiratory gases or vapours by influencing the temperature
    • A61M16/1085—Preparation of respiratory gases or vapours by influencing the temperature after being humidified or mixed with a beneficial agent
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
    • A61M16/10—Preparation of respiratory gases or vapours
    • A61M16/1075—Preparation of respiratory gases or vapours by influencing the temperature
    • A61M16/1095—Preparation of respiratory gases or vapours by influencing the temperature in the connecting tubes
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
    • A61M16/08—Bellows; Connecting tubes ; Water traps; Patient circuits
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
    • A61M16/10—Preparation of respiratory gases or vapours
    • A61M16/14—Preparation of respiratory gases or vapours by mixing different fluids, one of them being in a liquid phase
    • A61M16/16—Devices to humidify the respiration air
    • A61M16/162—Water-reservoir filling system, e.g. automatic
    • A61M16/164—Water-reservoir filling system, e.g. automatic including a liquid inlet valve system
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2205/00—General characteristics of the apparatus
    • A61M2205/33—Controlling, regulating or measuring
    • A61M2205/3368—Temperature
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2205/00—General characteristics of the apparatus
    • A61M2205/50—General characteristics of the apparatus with microprocessors or computers
    • A61M2205/502—User interfaces, e.g. screens or keyboards
    • A61M2205/505—Touch-screens; Virtual keyboard or keypads; Virtual buttons; Soft keys; Mouse touches

Definitions

  • Humidifier system for breathing air Humidifier system for breathing air.
  • This invention relates to a' compact, economical and efficient humidifier system for providing a supply of air at or near 100 percent relative humidity and a predetermined temperature to a medical (e.g. critical care) patient.
  • the humidifier system is of the type which is adapted to be interfaced with an artificial respirator (i.e. ventilator) such as that commonly found in an intensive care unit of a medical facility.
  • respirator i.e. ventilator
  • apparatus which is capable of delivering, to a patient, air that is characterized by substantially 100 percent relative humidity and a temperature of 35°C. That is, breatheable air that is highly saturated with water vapor will minimize the drying out of the mucous membranes located in the patient's respiratory tract so as to lessen the chance of injury to delicate tissues and thereby reduce the possibility of an obstruction in the patient's breathing passage as a consequence of insufficient mucous flow.
  • various humidifier devices are available to be interfaced with a ventilator for heating and humidifying a supply of air for delivery to a patient.
  • a ventilator for heating and humidifying a supply of air for delivery to a patient.
  • certain conventional devices known as pot humidifiers, require a large reservoir supply of water (e.g. as much as 300 to 600 cc) to be heated for the purpose of generating water vapor. Due to the large thermal mass created by such a large reservoir supply, pot humidifiers are generally cumbersome and energy inefficient and usually require a relatively lengthy period of time from start-up before the reservoir water supply can be heated to a temperature suitable for producing vapor.
  • wick humidifiers utilize an absorbent wick for the purpose of reducing the size of the reservoir water supply.
  • absorbent wick for the purpose of reducing the size of the reservoir water supply.
  • the wick is formed from blotting paper which is positioned in contact with a source of heat so as to permit the wick to rapidly reach operating temperature.
  • blotting paper is typically not reusable and both the cost of maintenance and time for reconditioning the wick humidifier are correspondingly increased.
  • Still other conventional humidifier devices lack the ability to precisely control the temperature of the air being delivered to the patient. Such devices do not include means to accurately sense the temperature of the air at both the humidifier outlet and patient ends of an air delivery (e.g. tubing) system. Thus, temperature variations which are frequently produced by changes in the air flow between the humidifier and the patient are often overlooked.
  • U.S. Patent No. 3,434,471 discloses a humidifier for use with a ventilator.
  • the humidifier includes a reservoir with a heat exchanger and heater.
  • Air to be humidified is passed into the heat exchanger, whereupon it is heated.
  • the heated air then passes above the water in the reservoir.
  • the air becomes saturated with water vapor and is passed through a second heat exchanger, whereupon it is cooled to cause some moisture to "rain out” and thereby assure 100 percent relative humidity at the temperature at which the air exits the humidifier.
  • the temperature of the air at the patient end is sensed by a thermistor which controls the output of the heater.
  • U.S. Patent No. 3,638,926 discloses humidification and heating apparatus which comprises a spirally wound resistance-heated plate in thermal contact with a sheet of water absorbent blotting paper. Air from a respirator travels along a spiral passage formed by the plate, the water surface at a reservoir, and a lid to produce a substantially saturated vapor at a desired temperature.
  • U.S. Patent- Nos. 4,248,217 and 4,305,388 generally relate to devices for controlling the heating of inspiratory gas as a function of the expiratory gas temperatures. Thermistors are used in each of the inspiratory and expiratory flow paths for sensing and controlling the heating of the gas.
  • the present humidifier system is adapted to be interfaced with an artificial respirator (e.g. a ventilator) to deliver air at nearly 100 percent relative humidity and at a predetermined temperature to a patient, such as at an intensive care unit of a medical facility.
  • the system includes a humidifier chamber and a heater assembly extending therewithin.
  • the humidifier chamber has a reservoir in which a relatively small supply of water is heated and boiled by the heater assembly.
  • the heater assembly extends through the reservoir and contacts the water supply to quickly boil the water supply and thereby produce vapor.
  • a vapor storage chamber is centrally disposed in the humidifier chamber and communicates with the reservoir for receiving a supply of vapor therefrom and with an inlet port for receiving a supply of incoming air from the ventilator, so that a supply of vapor saturated air is supplied at the vapor storage chamber.
  • a continuous heat exchange surface spirals outwardly through the humidifier chamber from the centrally disposed vapor storage chamber to a peripherally disposed air outlet port.
  • the vapor saturated air condenses as it traverses the heat exchange surface until heated air, at substantially 100 percent relative humidity, is provided at the air outlet port of the humidifier chamber.
  • a tube extends between the air outlet port and the patient by which to deliver outgoing humidified air to the patient.
  • the tube includes a heating element by which to heat the outgoing air to avoid condensation in the tube and minimize temperature fluctuations in the outgoing air being delivered to the patient.
  • the humidifier system also includes microprocessor based control circuitry having a pair of drivers for energizing the heater assembly and the heating element of the tube.
  • First and second temperature sensors are responsive to the temperature of the outgoing humidified air at the humidifier chamber outlet port and the patient end of the tube, respectively.
  • the temperatures sensed are compared with one another and with a predetermined temperature by a closed loop, dual servo controller for the purpose of regulating the duty cycle of and output power provided by the pair of drivers for controlling the energization of the heater assembly and the heating element of the tube. Therefore, the heat provided by the heater assembly and heating element of the tube can be adjusted, so that the outgoing humidified air can be delivered to the patient at the predetermined temperature and with minimum temperature fluctuation.
  • the control circuitry also includes a plurality of indicator lamps located at a control panel of a housing, whereby the performance of the humidifier system can be monitored and visually displayed.
  • FIG. 1 is an isometric view illustrative of the housing and humidifier chamber which form part of the humidifier system of the present invention
  • FIG. 2 is a front elevation of a base portion which forms part of the humidifier chamber of FIG. 1;
  • FIG. 3 is a cross-section of a shroud portion which forms the remaining part of the humidifier chamber of FIG. 1;
  • FIG. 4 is a bottom view of the shroud portion of the humidifier chamber of FIG. 1;
  • FIG. 5 is an isometric view of the main heating assembly which is disposed within the base portion of the humidifier chamber of FIG. 1;
  • FIG. 6 is a . cross-section of the main heater assembly taken along lines 6-6 of FIG. 5 to illustrate the relative alignment of the electrical components which are housed therein;
  • FIG. 7 is an end view of the main heater assembly taken along lines 7-7 of FIG. 5;
  • FIG. 8 is a block diagram which is representative of the control circuitry which also forms part of the presently disclosed humidifier system.
  • FIG. 9 is a schematic of a closed loop, servo-controlled system of the present invention for controlling the temperature of the humidified air that is supplied from the humidifier to the patient.
  • FIG. 1 illustrates the housing for the present humidifier system.
  • Housing 1 includes a cavity 4 and recess 6 molded therein and adapted for the removable receipt of a humidifier chamber 8.
  • chamber 4 comprises a cylindrical shroud portion 30 and a generally tapered base portion 31.
  • Shroud portion 30 is located above the cavity 4 and within the recess 6 of housing 1.
  • Base portion 31 (only a portion of which is shown in FIG. 1) extends from the interior of cavity 4 to a releasable connection with shroud portion 30.
  • a concentrically aligned air inlet port 32 Projecting upwardly from and coextensively formed with the cylindrical shroud portion 30 is a concentrically aligned air inlet port 32.
  • inlet port 32 is interfaced with a ventilator source, such as a mechanical lung, or the like, so as to receive a supply of incoming air by way of an air hose (not shown) .
  • a peripherally disposed air outlet port 34 Also projecting upwardly from and coextensively formed with shroud portion 30 is a peripherally disposed air outlet port 34.
  • Outlet port 34 is shown interconnected with a flexible heating tube 36 at a coupling member 38.
  • Heating tube 36 is preferably fabricated from silicone and is adapted to be sterilized (e.g. such as in an autoclave) so as to be reusable.
  • Heating tube 36 has a length which is typically between four to six feet and terminates at a cuff 40 through which outgoing humidified air is supplied from outlet port 34 to the patient. Extending through heating tube 36 in a forward direction and then being bent backwards upon itself in a reverse direction is an optional heater element 42 (shown dotted) . The heat provided by element 42 advantageously prevents the formation of condensation along the path of heating tube 36. Heater element 42 also compensates for temperature loss of the humidified air being conveyed between outlet port 34 and cuff 40.
  • heater element 42 generates heat which is equivalent to the heat dissipated along the heating tube 36 to the atmosphere, whereby to reduce temperature fluctuations and maintain the outgoing humidified air being delivered from humidifier chamber 8 to the patient at a substantially uniform temperature (e.g. 35°C) .
  • a substantially uniform temperature e.g. 35°C
  • conventional electrical wiring 44 is interconnected between a source of current at housing 1 and heater element 42 at coupling 38. Wiring 44 provides electrical current by which to energize heater element 42 and thereby heat the outgoing humidified air which passes through heating tube 36 to the patient.
  • the temperature of the humidified air is controlled and maintained at a predetermined temperature (e.g.
  • an outlet temperature probe e.g. a thermistor 10 is associated with outlet port 34 to sense the temperature of the humidified air exiting humidifier chamber 8.
  • a proximal temperature probe e.g. a thermistor 12 is associated with cuff 40 to sense the proximal temperature of the humidified air being delivered to the patient from heating tube 36.
  • the cuff 40 is typically connected to a Y-shaped patient wye (only a portion of which is shown) .
  • One leg of the patient wye 14 supplies air to the respiratory system of the patient and (as illustrated) is in contact with temperature probe 12.
  • the other leg (not shown) of coupling 14 is used to convey exhaust gases during the exhalation portion of the patient's breathing cycle.
  • Each of the outlet and proximal temperature probes 10 and 12 is interconnected with control housing 1 via conventional wiring 16 for supplying temperature related information to the humidifier system control circuitry which, as will soon be described, is adapted- to control the air temperature so that the patient is supplied with humidified air at a particular, predetermined temperature (e.g. 35°C) .
  • a delivery tube 20 is connected between a remote water source and the base 31 of humidifier chamber 8 at a water intake spout 21.
  • the water source (not shown) may be, for example, a disposable bag or bottle which is positioned or hung relative to control housing 1, such that water is supplied to delivery tube 20 under the influence of gravity.
  • Delivery tube 20 is interfaced with a solenoid operated, normally closed pinch valve 22 which is periodically opened to permit a measured volume of water (e.g. approximately 2 cc) to be controllably delivered by way of tube 20 and intake spout 21 to a humidifier chamber water reservoir (best shown in FIG. 2) at the interior of the base portion 31.
  • a measured volume of water e.g. approximately 2 cc
  • Control panel 23 is positioned at housing 1 to permit easy operation and observation by appropriate medical personnel.
  • Control panel 23 includes a keyboard having four pressure activated touch pads 24 (designated SET TEMP), 25-1, 25-2, and 29 (designated RESET/RECALL) .
  • the touch pads permit adjustment of the predetermined temperature of the humidified air to be delivered to the patient.
  • Control panel 23 also includes a ' digital temperature display 26 (designated PROX TEMP) at which either the predetermined or actual temperature of the humidified air to be delivered to the patient can be selectively indicated.
  • control panel 23 Also included at control panel 23 are four light emitting diode indicator lamps 28-1 (designated POWER) , 28-2 (designated WATER) , 28-3 (designated HI TEMP) , and 28-4 (designated INOP) .
  • the indicator lamps provide a visual indication and/or warning regarding various humidifier system operating conditions. Details relating to the particular function and operation of control panel 23 and the aforementioned components thereof will be disclosed hereinafter when referring to FIG. 8 of the drawings.
  • the humidifier system housing 1 also includes a main on-off switch 2 by which to manually control the supply of electrical power from an AC source to the soon to be described control circuitry at housing 1. Moreover, housing 1 is also provided with an alarm 3 by which to provide audible warning signals in the event of the occurrence of certain undesirable system operating conditions, the nature of which will also soon be described.
  • Humidifier chamber 8 is now described while referring to FIGs. 2-4 of the drawings.
  • humidifier chamber 8 comprises a generally cylindrical shroud portion 30 (best illustrated in FIGs. 3 and 4) and a generally tapered base portion 31.
  • Projecting upwardly from the top of shroud portion 30 are the air inlet and outlet ports 32 and 34.
  • air inlet port 32 is adapted to be interfaced with a ventilator, so as to receive a supply of incoming air therefrom.
  • air outlet port 34 is adapted to be interfaced with heating tube 36 (of FIG. 1) for delivering humidified air to the patient.
  • Base portion 31 includes an annular flange 46 or cover extending around the periphery at the top end thereof.
  • Annular flange 46 has a diameter which is slightly larger than that of the shroud portion 30.
  • the bottom of shroud portion 30 is of suitable dimension to be removably received and retained within the annular flange 46 of base portion 31.
  • a sealing O-ring 48 may be disposed between the flange 46 and the bottom of shroud portion 30, so as to seal the shroud portion 30 within base portion 31.
  • Base portion 31 includes a hollow, cylindrical water reservoir 50 formed at the bottom end thereof. Projecting upwardly from reservoir 50 is the water intake spout 21 which is to be interfaced with a water delivery tube (designated 20 in FIG. 1) , so that a small supply (e.g. 2 cc) of water can be provided from a source thereof to reservoir 50. Located between reservoir 50 and annular cover flange 46 is a hollow, cylindrical water return reservoir 52. The diameter of water return reservoir 52 is preferably larger than that of reservoir 50. Water reservoirs 50 and 52 communicate with one another for a purpose that will soon'become apparent.
  • heater assembly 54 Extending through reservoirs 50 and 52 and projecting outwardly from the bottom end of base portion 31 is the main heater assembly 54 (the details of which will be described in greater detail when referring to FIGs. 5-7 of the drawings) .
  • heater assembly 54 is comprised of a housing portion 64 and a connector portion 66.
  • the housing and connector portions 64 and 66 are connected together by a retaining ring 68 which is surrounded by and coupled to a clamp 59 for the purpose of securing heater assembly 54 to the base portion 31 of humidifier chamber 8 (best shown in FIG. 5) .
  • Water delivered via intake spout 21 to reservoir 50 is heated and boiled therein by heater assembly 54.
  • the steam generated as a result of such boiling water passes from reservoir 50 to the humidifier chamber heat exchange path which is located within shroud portion 30, the details of which are now described.
  • humidifier chamber portion 30 comprises a continuous heat exchange contact surface 56 which spirals outwardly from a distal end at a centrally disposed and cylindrically shaped vapor storage chamber 58 to a proximal end at air outlet port 34.
  • the heat exchange spiral 56 is preferably fabricated from polysufone (as is shroud portion 30) and provides a continuous contact surface of approximately 20 inches in the presently described embodiment.
  • the vapor storage chamber 58 includes a plurality of fingers 60 which project radially inwardly.
  • Finger 60 terminate so as to form a gap 62 therebetween which extends axially throughout chamber 58.
  • Vapor storage chamber 58 is coextensively formed and concentrically aligned with air inlet port 32, so that incoming air supplied by a ventilator is delivered to the vapor storage chamber 58 and the gap 62 formed between the fingers 60.
  • the outermost or proximal end (relative to the centrally disposed vapor storage chamber 58) of the spiralling contact surface 56 of shroud portion 30 communicates with air outlet portion 34, whereby humidified air can be supplied at a predetermined temperature (e.g. 35°C) to the patient by way of outlet port 34 and the heating tube (designated 36 in FIG. 1) .
  • a predetermined temperature e.g. 35°C
  • temperature probes 10 and 12 are respectively interfaced with outlet port 34 and the patient wye 14 (of FIG. 1) , so that the temperature of the humidified air being delivered to the patient via heating tube 36 can be sensed and controlled for the purpose of achieving a predetermined air temperature as set at the control panel (designated 23 in FIG. 1) of housing 1.
  • the manner by which the temperature of the humidified air is sensed and controlled for providing the patient with air having the predetermined temperature will be described when referring to FIG. 9 of the drawings.
  • heater assembly 54 comprises a heater housing portion 64 and a connector portion 66.
  • the heater housing portion 64 is preferably fabricated from aluminum which is anodized with a suitable impregnation coating.
  • the connector portion 66 is preferably fabricated from plastic.
  • the housing and connector portion 64 and 66 are adapted to be sandwiched together by a plastic retaining ring 68 which surrounds heater assembly 54 and is ultrasonically welded to connector portion 64.
  • Retaining ring 68 is surrounded by and coupled to a clamp 69 at respective coextensively formed, cylindrical bosses 70 and 71.
  • a locking and pivot pin 72 is inserted through an alignment of the bosses 70 and 71 of retaining ring 68 and clamp 69 to prevent a disengagement therebetween.
  • clamp 69 functions to secure the main heater assembly 54 within the base portion 31 of humidifier chamber 8.
  • An O-ring 73 surrounds heater assembly 54 between the housing and connector portions 64 and 66 to form a- more secure water-tight connection and prevent leakage from the reservoir water supply of humidifier chamber 8 when heater assembly 54 is extended therethrough.
  • the housing portion 64 of main heater assembly 54 includes the spaced arrangement of a heating element 74, a water refill thermistor 76, a microfuse 78, and a ground terminal 80.
  • the heating element 74 is preferably a conventional 200 watt resistance heater, such as that manufactured by Watlow Corporation. With main heater assembly 54 positioned in the assembled relationship at humidifier chamber 8 (of FIG. 2) , heating element 74 is adapted to generate sufficient heat to quickly boil the relatively small supply contained by reservoir 50 of the humidifier chamber base portion 31.
  • the water refill thermistor 76 is adapted to sense an increase in temperature (e.g. beyond 110°C) corresponding to a depletion of the water supply at reservoir 50.
  • Refill thermistor 76 thereby provides an indication that reservoir 50 must be refilled with additional water from the source thereof.
  • Microfuse 78 has a temperature sensitive, chemical fuse link which is adapted to rupture at excessive (e.g. above 150°C) heater assembly temperatures, whereby to de-energize the main heater element 74 and interrupt the supply of heat for boiling water in reservoir 50.
  • An example of such a microfuse is Model No. 4300 manufactured by Micro Devices Corporation.
  • microfuse 78 is included within the main heater assembly 54 to prevent damage to the humidifier chamber should heating element 74 overheat as a consequence of an undesirable operating condition during the utilization of the presently described humidifier system.
  • Ground terminal 80 is electrically interconnected with the aluminum casing of the heater housing portion 64 of main heater assembly 54.
  • Extending through the connector portion 66 of main heater assembly 54 for electrical connection with the heating element 74, refill thermistor ' 76, microfuse 78, and ground terminal 80 are a plurality of five electrical connector pins 81-85 (best illustrated in FIG. 7) by which electrical power is supplied to assembly 54. More particularly, the heater assembly heating element 74 and the microfuse 78 are connected in electrical series between a first pair of connector pins 81 and 85, such that an open circuit caused by a rupture of the chemical fuse link of microfuse 78 in response to an overheating of element 74 will result in a termination of the current supply to heating element 74 and a discontinuation of the heating operation. Water refill thermistor 76 is electrically connected between a second pair of connector pins 82 and 84. Ground terminal 80 is electrically connected between the fifth connector pin 83 and the casing of the heater housing portion 64, as previously indicated.
  • the reservoir 50 of humidifier chamber base . portion 31 is initially devoid of water.
  • Current is drawn by the heating element 74 of main heater assembly 54 so as to cause the temperature of heater assembly 54 to be raised beyond 110°C.
  • This increased temperature is sensed by the water refill thermistor 76 of main heater assembly 54 so as to provide an indication that reservoir 50 must be filled with water from the remote source thereof.
  • the solenoid . operated pinch valve (designated 22 in FIG. 1) at housing 1 is opened for a time sufficient to permit an amount (e.g. 2 cc) of water to be provided to reservoir 50 from the source thereof by way of delivery tube 20 and water intake spout 21.
  • the relatively small water supply at reservoir 50 of base portion 31 is subsequently boiled by the main heater assembly 54, and the resulting steam is conveyed to the vapor storage chamber 58 of shroud portion 30.
  • a supply of vapor is deposited in the vapor storage chamber 58 of the humidifier chamber shroud portion 30.
  • the vapor at storage chamber 58 is over-heated and over-humidified (beyond the predetermined set points) , so as to cause a thin layer of water to form around the surface of chamber 58. Excess water is drained, by means of gravity, from vapor storage 58 to the water return reservoir 52 (of FIG. 2) of base portion 31 where it may be reboiled and revaporized.
  • inspiration i.e. when incoming air is supplied to the air inlet port 32 of shroud portion 30 by a ventilator
  • air is pumped through the gap 62 of vapor storage chamber 58 where it acquires an excess of vapor.
  • the vapor saturated air is then supplied to the distal end of the spiral heat exchange contact surface 56 of shroud portion 30.
  • water will rain out (condense) from the vapor saturated air as it traverses the spiral path of the continuous and relatively cooler heat exchange surface 56 so as to -assure 100 percent relative humidity.
  • Such water is drained, by means of gravity, from the heat exchange surface 56 of shroud portion 30 to the water return reservoir 52 of base portion 31 to be reheated thereat.
  • the temperature of the outgoing humidified air decreases around spiralling contact surface 56 until the temperature of the air at the proximal or patient end of contact surface 56 is approximately equal to the surface temperature of that portion of humidifier chamber 8 which communicates with air outlet port 34. That is, vapor which is initially characterized by high density and temperature migrates through heat exchange surface 56 from vapor storage chamber 58 to air outlet port 34. During such migration and contact with heat exchange surface 56, the density and temperature of the vapor decrease.
  • the relative humidity and temperature of the outgoing air supplied from outlet port 34 to the heating tube 36 for delivery ' to the patient can be accurately controlled depending upon the length of the path established by spiralling contact surface 56 for achieving the preferred (100 percent) relatively humidity and (35°C) temperature.
  • the microprocessor based control circuitry of FIG. 8 is preferably implemented on printed circuit boards which are located at the interior of humidifier system housing 1.
  • the control circuitry includes a control panel (designated 23 in FIG. 1) which is positioned at housing 1 to permit easy access to and inspection by attendant medical personnel.
  • the control panel includes touch pads 24, 25-1, 25-2, and 29; digital display 26; and light emitting diode (LED) indicator lamps 28-1, 28-2, 28-3, and 28-4.
  • the humidifier system software automatically presets the proximal air temperature (i.e. the temperature of the humidified air to be delivered to the patient from patient wye 14 at 35°C.
  • the user wishes to change the proximal temperature from the aforementioned preset temperature, he depresses the SET TEMP touch pad 24 at the same time that he depresses either touch pad 25-1 (to increase the preset proximal temperature) or touch pad 25-2 (to lower the preset proximal temperature) .
  • the new, manually set proximal temperature will be displayed by digital display 26.
  • display 26 indicates the actual proximal temperature, as sensed by the proximal temperature probe (i.e. thermistor) 12 at patient wye 14.
  • the (green) POWER indicator lamp 28-1 at control panel 23 is illuminated.
  • the (yellow) WATER indicator lamp 28-2 at control panel 23 is illuminated.
  • the predetermined temperature either 35°C or that manually set after depressing SET TEMP touch pad 24
  • the (red) HI TEMP indicator lamp 28-3 at control panel 23 is illuminated.
  • the (red) INOP indicator lamp 28-4 at control panel 23 is illuminated.
  • an audible warning signal is simultaneously provided by the alarm (designated 3 in FIG. 1) during the occurrence of any of the previously-mentioned undesirable humidifier system operating conditions.
  • the system software may also cause alarm 3 to be sounded in the event that either of the proximal temperature (sensed by thermistor 12) or the humidifier chamber outlet temperature (sensed by thermistor 10) drops below a predetermined temperature limit (e.g. 7°C) ; the temperature of the main heater assembly 54 (sensed by thermistor 76) exceeds or drops below a predetermined temperature limit (e.g. 150°C and 7°C, respectively) , or the system fails to complete a software-controlled self-test routine.
  • a predetermined temperature limit e.g. 7°C
  • indicator lamps 28-2, 28-3, and 28-4 and/or alarm 3 indicates the need for manual intervention, inspection, and possible correction of the _undesirable operating condition.
  • the indicator lamps 28-2, 28-3, and 28-4 and/or the alarm 3 will remain energized until the undesirable condition is remedied and the user depresses the RESET/RECALL touch pad 29 at the keyboard of control panel 23.
  • Vapor generator heater driver 88 preferably comprises a pair of MCR72-6 silicon controlled rectifiers, such as that manufactured by Motorola Corporation, which are electrically interconnected in series (for redundency) with the heating element 74 of the main heater assembly (54 in FIG. 5) .
  • Heater driver 88 supplies current to heating element 74, so that the reservoir water supply can be boiled and vapor subsequently generated within humidifier chamber 8.
  • the transformer 90 is preferably characterized by a primary winding having a 120/240 volt capacity and a secondary winding having a 24 volt center tap connection.
  • AC output voltage from the secondary winding of transformer 90 is supplied to power each of a tube heater driver 92 and a water solenoid driver 94.
  • the tube heater driver 92 preferably comprises an MCR72-6 silicon controlled rectifier, such as that manufactured by Motorola Corporation, which is electrically interconnected with the heater element 42 of the heating tube (36 of FIG. 1) in the event that optional heater element 42 is to be utilized.
  • Tube heater driver 92 controls the supply of current to heater element 42 so that the heat generated thereby is adapted to avoid condensation and reduce temperature fluctuations of humidified air within the heating tube 36 (of FIG. 1) .
  • the water solenoid driver 94 preferably comprises a TIP120 Darlington transistor, such as that manufactured by Motorola Corporation, which is electrically interconnected with a solenoid 96.
  • Solenoid 96 is interfaced with solenoid controlled pinch valve 22 at ' housing 1.
  • pinch valve 22 is periodically opened for a time sufficient to permit a controlled amount (e.g. 2 cc) of water to be added to the reservoir of humidifier chamber 8 via delivery tube 22 and water intake spout 21.
  • a controlled amount e.g. 2 cc
  • water solenoid driver 94 energizes solenoid 96 to cause pinch valve 22 to be opened and the humidifier chamber reservoir to be replenished (by means of gravity) from a water source.
  • the reservoir fail to receive an additional supply of water (e.g. because the source is empty) , the reservoir temperature will continue to rise to 130°C at which temperature the aforementioned LED indicator lamp 28-2 at the control panel 23 of housing 1 is illuminated, so as to provide a visual warning of the depleted reservoir water supply.
  • the output voltage from transformer 90 is also rectified, such as by means, of a full wave rectifier (not shown) , for supplying DC power (e.g. 12 volts DC) for driving alar 3, digital display 26, and LED indicator lamps 28-1, 28-2, 28-3, and 28-4.
  • a rectified DC voltage (e.g. 0-2 volts) is also supplied from transformer 90 to an input terminal of an analog to digital converter 98 to provide converter 98 with a source of reference potential.
  • analog to digital converter 98 is preferably a single slope converter, such as a 14443 microelectronic chip manufactured by Motorola Corporation.
  • analog to digital converter 98 is adapted to provide an output pulse, the width of which is proportional to the voltage level of a selected one of a plurality (e.g. six) of input signals.
  • Three input signals are respectively applied to corresponding input terminals of analog to digital converter 98 from a pair of opto-isolators 100 and 102.
  • Opto-isolator 100 is electrically interfaced with the heating element 74 (of heater assembly 54)
  • opto-isolator 102 is electrically interfaced with each of the heater element 42 (of heating tube 36) and solenoid 96.
  • Each of opto-isolators 100 and 102 is preferably an H11G2 microelectronic chip, such as that manufactured by Motorola Corporation, which includes a light emitting diode optically coupled to a semiconductor switching device.
  • Opto-isolators 100 and 102 are adapted to monitor the state (i.e. sense current drawn by) of resistance elements 74 and 42 and inductance element 96.
  • linearization and amplification circuit 104 linearizes and amplifies, via respective CA3260AE high gain amplifiers (such as that manufactured by RCA Corporation) , the three non-linear signals which are indicative of the temperature of the humidified air at the outlet port 34 of humidifier chamber 8 (sensed by thermistor 10) , the proximal temperature of the humidified air being delivered to the patient from heating tube 36 (sensed by thermistor 12) , and the temperature of main heater assembly heating element 74 (sensed by thermistor 76) .
  • CA3260AE high gain amplifiers such as that manufactured by RCA Corporation
  • the control circuit microprocessor unit 106 is electrically interconnected with analog to digital converter 98 so as to enable converter 98 (via an output line designated START) and to receive information (via an input line designated CONVERT) from which the proximal temperature of the humidified air being delivered to the patient can be sensed and subsequently adjusted in accordance with the system software (the nature of which will be explained when referring to FIG. 9 of the drawings) .
  • Microprocessor unit 106 is preferably a 146805E2 microelectronic chip which is interfaced with an auxilary 2732 EPROM microelectronic chip (both chips being readily available commercially to provide memory for storing the system software.
  • Microprocessor unit 106 is also connected to transformer 90 so as to receive a signal (via an input line designated LINE FREQ) which is indicative of the frequency (e.g. zero crossings) of the rectified DC voltage provided thereby, so that the AC line voltage and the DC rectified voltage can be monitored to assure the presence of suitable operating voltage levels.
  • Output signals from microprocessor unit 106 are provided to control the operations of the alarm 3, display 26, and LED indicator lamps 28-2 and 28-3, vapor generator driver 88, tube heater driver 9 ' 2, water solenoid driver 94, and an INOP circuit 108.
  • a microprocessor controlled circuit 108 (designated INOP) .
  • the INOP circuit 108 is preferably a 7555 microelectronic chip, such as that manufactured by General Electric Intersil Corporation, utilized as a one-shot multivibrator.
  • the INOP circuit 108 is activated to deenergize vapor generator heater driver 88, tube heater driver 92, and water solenoid driver 94 to prevent the additional delivery of water and the continued heating thereof at the reservoir of humidifier chamber 8 so as to avoid the possibility of damage to chamber 8 until the undesirable operating condition has been remedied.
  • the INOP multivibrator circuit 108 is retriggered in response to a train of input pulses supplied from microprocessor unit 106 during the occurrence of conditions which are indicative of normal humidifier system operation.
  • the output of INOP circuit 108 in response to the pulse train is a relatively HI logic level signal.
  • the INOP multivibrator will time out, and will put out a relatively LOW logic level signal, to deenergize drivers 88, 92, and 94 and prevent further humidifier system operation until a correction is made.
  • the aforementioned LED indicator lamp 28-4 at the control panel 23 of housing 1 is illuminated (and alarm 3 may also be sounded) , so as to provide to attendant medical personnel a visual warning of the occurrence of such an undesirable operating condition.
  • Microprocessor unit 106 is interfaced with display 26 (as already indicated) and a shift register 110, so that information can be displayed regarding the predetermined air temperature and the actual proximal temperature of the humidified air being supplied to the patient, (as sensed by thermistor 12) .
  • Shift register 102 is preferably a 74HC164 microelectronic chip, such as that manufactured by Motorola Corporation, which is adapted to scan the keyboard (comprising touch pads 24, 25-1, 25-2, and 29), so as to determine the entry of any change in the present proximal temperature, whereby either of the preset temperature (i.e. 35°C) or the new, manually set temperature can be indicated at display 26.
  • servo controller 120 includes a first comparator 122 which receives a pair of input signals.
  • a first input signal (designated T réelle) supplied to comparator 122 is indicative of either the temperature (i.e. 35°C) as preset by the system software or a newly set temperature as entered manually at the keyboard of control panel 26 (of FIG. 1) .
  • the second input signal (designated T ) supplied to comparator 122 is indicative of the actual proximal temperature of the humidified air (as sensed by proximal temperature thermistor 12) .
  • the output of comparator 122 is an error signal (designated e,) which is indicative of the difference between the magnitudes of the input signals T _ and T .
  • This error signal e. is applied to a floating controller 124.
  • Controller 124 is adapted to convert the error signal e, from comparator 122 into a temperature signal which is proportional to such error.
  • the output signal (designated T ⁇ ) from controller 124 is a software determined temperature which represents an estimate of a set point temperature to which the humidified air must be heated at the outlet port 34 of humidifier chamber 8 (of FIG. 1) in order to ultimately achieve the desired proximal temperature T .
  • This estimated, software established set point temperature T réelle g at output port 34 may be represented as follows:
  • T HS T PS + K l e l + 1/K, ⁇ e-_dt;
  • K, and K ? are constants.
  • the output signal T from controller 124 is supplied to a first input terminal of a second comparator 126. Supplied to a second input terminal of comparator 126 is a signal (designated T soup) which is indicative of the actual temperature of the humidified air at the outlet port 34 of humidifier chamber 8 (as sensed by thermistor 10) .
  • the output of comparator 126 is another error signal (designated e «) which is indicative of the difference between the magnitudes of the input temperatures T s and T trash.
  • This error signal e ⁇ is supplied to another controller 128. Controller 128 is adapted to control the input power to main heater assembly 54 by providing an input signal (designated P ⁇ ) to vapor generator heater driver 88 (of FIG.
  • K-., K. and K-. are constants.
  • the temperature of the humidified air, which is heated by the main heater assembly 54, is sensed by thermistor 10 at the air outlet port 34 of humidifier chamber 8 and, as previously disclosed, a signal T R , which is representative of this temperature, is fed back via a first feedback path to an input terminal of comparator 126.
  • the temperature of the humidified air which is heated by heating tube 36 and delivered to the patient is sensed by thermistor 12 at the patient wye 14 (of FIG. 1) and, as previously disclosed, a signal T_, which is representative of this temperature, is fed back via a second feedback path to an input terminal of comparator 122.
  • the power level or duty cycle of the tube heater driver 92 (of FIG. 8) is controlled by a software generated signal (designated Pm HD ⁇ s ) , which signal may be represented as follows:
  • K6, and K_7 are constants.
  • a relatively large temperature drop (T Design-T p ) across heating tube 36 typically signifies excess moisture therein, whereby power to the tube heater driver is increased to eliminate condensation from tube 36.
  • a relatively small temperature drop across heating tube 36 typically signifies little condensation within the tube and an outlet air temperature having 100 percent relative humidity. Therefore, power to the tube heater driver is reduced to avoid drying of and possible damage to the tube 36.
  • the presently disclosed humidifier system eliminates the shortcomings which are characteristic of conventional humidifier systems. That is, the present humidifier system has a relatively low cost, compact configuration which utilizes a permanent, reusable wick and a relatively small reservoir supply of water which can be rapidly heated to operating temperature.
  • the system housing includes a control panel which is convenient to operate and provides easily read indications of system performance.
  • the control circuitry provides a dual servo controller having two feedback paths to permit accurate monitoring and control of the proximal temperature of the patient air relative to a predetermined temperature, while maintaining substantially 100 percent relative humidity over a range of suitable air temperatures.

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  • Health & Medical Sciences (AREA)
  • Emergency Medicine (AREA)
  • Pulmonology (AREA)
  • Engineering & Computer Science (AREA)
  • Anesthesiology (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Hematology (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Air Humidification (AREA)

Abstract

Un système humidificateur comprend une chambre d'humidification (8), un agencement de chauffage, des circuits de commande (23) par microprocesseur, et un boîtier (1) pour les circuits de commande. L'humidificateur d'air fournit de l'air avec une humidité relative presque égale à 100 pour cent, à une température prédéterminée (35oC par exemple), à un patient soumis à des soins médicaux (en état critique par exemple). La chambre d'humidification (8) comprend un trajet continu en spirale d'échange de chaleur allant d'une chambre de stockage de vapeur à un orifice d'évacuation (34) de la chambre d'humidification (8) connecté à un tube (36) de chauffage de l'air, pour que l'air évacué puisse être fourni au patient. La chambre de stockage de vapeur est en contact avec un ventilateur, source de l'air admis par l'orifice d'admission (32), et avec un réservoir relativement petit dans lequel une quantité d'eau est mise en ébullition par l'agencement de chauffage pour fournir l'air saturé de vapeur de la chambre de stockage de vapeur au trajet d'échange de chaleur. Les circuits de commande comprennent une paire de senseurs (10, 12) sensibles à la température de l'air humidifié évacué par l'orifice d'évacuation (34) de la chambre d'humidification et à la température du tube de chauffage (36) à l'extrémité proche du patient. Les températures détectées sont utilisées pour commander l'activation de l'agencement de chauffage et d'un élément de chauffage (42) du tube de chauffage (36), pour que l'air humidifé puisse être fourni au patient à la température prédéterminée et avec une quantité minimale de retombées de condensation.
EP85905291A 1984-11-01 1985-10-16 Systeme humidificateur d'air destine a la respiration Expired - Lifetime EP0201529B1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US06/667,142 US4621632A (en) 1984-11-01 1984-11-01 Humidifier system
US667142 1984-11-01

Publications (2)

Publication Number Publication Date
EP0201529A1 true EP0201529A1 (fr) 1986-11-20
EP0201529B1 EP0201529B1 (fr) 1991-08-21

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US (1) US4621632A (fr)
EP (1) EP0201529B1 (fr)
JP (1) JPS62500702A (fr)
CA (1) CA1225303A (fr)
DE (1) DE3583862D1 (fr)
WO (1) WO1986002566A1 (fr)

Families Citing this family (184)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
AU581986B2 (en) * 1985-05-22 1989-03-09 Fisher & Paykel Healthcare Limited Improvements in or relating to methods of and/or apparatus for humidifying gases
GB2192136B (en) * 1986-07-04 1991-01-02 Virotherm Lab Ltd Medical breathing apparatus
DE3730551A1 (de) * 1987-09-11 1989-03-30 Annedore Kinnle Med Techn Zube Atemgasbefeuchtungsgeraet
US4867152A (en) * 1987-10-09 1989-09-19 The Boc Group, Inc. Respiratory therapy apparatus with selective display of parameter set points
US4829998A (en) * 1988-02-25 1989-05-16 Jackson Richard R Delivering breathable gas
US5031612A (en) * 1990-04-24 1991-07-16 Devilbiss Health Care, Inc. System and method for delivering warm humidified air
JPH0653176B2 (ja) * 1990-11-30 1994-07-20 史朗 鈴木 加湿器
US5529060A (en) * 1991-05-22 1996-06-25 Fisher & Paykel Limited Humidifiers with control systems to prevent condensation
EP0535952B1 (fr) * 1991-10-04 1997-12-29 FISHER & PAYKEL LIMITED Humidificateur
US5287849A (en) * 1992-07-24 1994-02-22 Vortran Medical Technology, Inc. Medicinal aerosol delivery system and method of use
US5349946A (en) * 1992-10-07 1994-09-27 Mccomb R Carter Microprocessor controlled flow regulated molecular humidifier
US5724957A (en) * 1993-01-29 1998-03-10 Aradigm Corporation Intrapulmonary delivery of narcotics
US5934272A (en) * 1993-01-29 1999-08-10 Aradigm Corporation Device and method of creating aerosolized mist of respiratory drug
US5558085A (en) * 1993-01-29 1996-09-24 Aradigm Corporation Intrapulmonary delivery of peptide drugs
US5392770A (en) * 1993-06-29 1995-02-28 Clawson; Burrell E. Tubing circuit systems for humidified respiratory gas
GB2284356B (en) * 1993-11-22 1997-10-29 Fisher & Paykel Respiratory humidifier conduit
DE19534001B4 (de) * 1994-09-20 2006-05-18 Fisher & Paykel, East Tamaki Befeuchterkammer
WO1996013292A1 (fr) * 1994-10-28 1996-05-09 Aradigm Corporation Appareil et procede de creation d'un brouillard d'aerosol d'un medicament respiratoire
US5564415A (en) * 1995-06-07 1996-10-15 Lifecare International, Inc. Humidifier for a ventilator
AUPN344095A0 (en) * 1995-06-08 1995-07-06 Rescare Limited A humidifier
US5687714A (en) * 1995-10-10 1997-11-18 The United States Of America As Represented By The Department Of Health And Human Services Self-cleaning endotracheal tube apparatus
WO1997018001A1 (fr) * 1995-11-13 1997-05-22 Fisher & Paykel Limited Conduit respiratoire chauffant
JPH1028737A (ja) 1996-07-16 1998-02-03 Metoran:Kk 加湿調整ユニット、人工呼吸器用加湿器及び加湿調整ユニットの製造方法
JP3748466B2 (ja) 1996-08-23 2006-02-22 株式会社メトラン 加湿調整ユニット及び加湿調整ユニットの製造方法
US5896857A (en) * 1996-12-20 1999-04-27 Resmed Limited Valve for use in a gas delivery system
US6336454B1 (en) 1997-05-16 2002-01-08 Resmed Limited Nasal ventilation as a treatment for stroke
AU746572C (en) * 1997-06-17 2004-07-01 Fisher & Paykel Healthcare Limited Respiratory humidification system
US20040221844A1 (en) 1997-06-17 2004-11-11 Hunt Peter John Humidity controller
US10130787B2 (en) 1997-06-17 2018-11-20 Fisher & Paykel Healthcare Limited Humidity controller
EP2143459B1 (fr) 1997-06-17 2013-08-14 Fisher & Paykel Healthcare Limited Système d'humidification pour un respirateur
CA2619893C (fr) * 1997-06-17 2011-11-15 Fisher & Paykel Healthcare Limited Systeme d'humidification pour appareillage respiratoire
AUPO742297A0 (en) 1997-06-18 1997-07-10 Resmed Limited An apparatus for supplying breathable gas
DE19750536A1 (de) * 1997-11-14 1999-05-20 Hans J Effertz Sprachunterstützungsgerät
US7731704B2 (en) * 1998-05-19 2010-06-08 Lexion Medical, Llc Method and apparatus for delivering an agent to the abdomen
US7744557B2 (en) * 1998-05-19 2010-06-29 Lexion Medical, Llc Method and apparatus for delivering an agent to the abdomen
US6068609A (en) * 1998-05-19 2000-05-30 Douglas E. Ott Method and apparatus for conditioning gas for medical procedures having humidity monitoring and recharge alert
US7918816B2 (en) * 1998-05-19 2011-04-05 Lexion Medical, Llc Method and apparatus for delivering an agent to the abdomen
US9028437B2 (en) * 1998-05-19 2015-05-12 Lexion Medical, Llc Method for delivering an agent to the abdomen
US7250035B1 (en) * 1998-05-19 2007-07-31 Lexion Medical, Llc Method and apparatus for treating gas for delivery to an animal
US20050107767A1 (en) * 1998-05-19 2005-05-19 Ott Douglas E. Method and apparatus for delivering an agent to the abdomen
US6095505A (en) * 1998-07-15 2000-08-01 Pegasus Research Corporation Patient-end humidifier
USD419658S (en) * 1998-08-28 2000-01-25 Resmed Limited Humidifier
US6435180B1 (en) 1999-07-01 2002-08-20 J&M Distributors Limited Method and apparatus for delivering humidified air to a face mask
DE10082260B4 (de) * 1999-08-05 2017-09-14 Resmed R&D Germany Gmbh System mit einer ersten Vorrichtung zur Zufuhr eines Atemgases und einer Befeuchtungsvorrichtung
MXPA02001881A (es) * 1999-08-23 2003-07-21 Fisher & Paykel Healthcare Ltd Controlador de humedad.
AUPQ339099A0 (en) 1999-10-13 1999-11-04 Resmed Limited A humidifier
DE10007506B4 (de) 2000-02-18 2006-02-02 Map Medizin-Technologie Gmbh Atemgasschlauchanordnung zur Zufuhr eines Atemgases
US6918389B2 (en) * 2000-03-21 2005-07-19 Fisher & Paykel Healthcare Limited Breathing assistance apparatus
US7559324B2 (en) 2000-06-21 2009-07-14 Fisher & Paykel Healthcare Limited Conduit with heated wick
US6976489B2 (en) 2000-06-30 2005-12-20 Northgate Technologies, Inc. Method and apparatus for humidification and warming of air
WO2002013898A2 (fr) * 2000-08-14 2002-02-21 Taga Medical Technologies, Inc. Humidificateur de dispositif cpap
US7708013B2 (en) 2000-12-08 2010-05-04 Vapotherm, Inc. Apparatus and method for delivering water vapor to a gas
DE10105383C2 (de) * 2001-02-06 2003-06-05 Heptec Gmbh Antischnarchgerät
US6935337B2 (en) 2001-02-16 2005-08-30 Resmed Limited Humidifier with structure to prevent backflow of liquid through the humidifier inlet
DE10139881B4 (de) 2001-08-20 2017-06-08 Resmed R&D Germany Gmbh Vorrichtung zur Zufuhr eines Atemgases und Verfahren zur Steuerung derselben
US7140367B2 (en) * 2002-02-20 2006-11-28 Fisher & Paykel Healtcare Limited Conduit overheating detection system
AU2003244171B2 (en) 2002-09-09 2007-11-15 Fisher & Paykel Healthcare Limited Limb for Breathing Circuit
US7347203B2 (en) * 2002-09-16 2008-03-25 Thayer Medical Corporation Heat and moisture filter exchanger and method
DK1562663T3 (en) * 2002-11-12 2016-04-18 Fisher & Paykel Healthcare Ltd Respiratory Aid Apparatus
US7493902B2 (en) 2003-05-30 2009-02-24 Fisher & Paykel Healthcare Limited Breathing assistance apparatus
WO2004108218A1 (fr) * 2003-06-11 2004-12-16 Fisher & Paykel Healthcare Limited Sonde et circuit de respiration
US7588033B2 (en) 2003-06-18 2009-09-15 Breathe Technologies, Inc. Methods, systems and devices for improving ventilation in a lung area
DE202004021795U1 (de) 2003-06-20 2011-02-10 ResMed Ltd., Bella Vista Atemgasvorrichtung mit Befeuchter
AU2003903139A0 (en) 2003-06-20 2003-07-03 Resmed Limited Breathable gas apparatus with humidifier
US6792946B1 (en) * 2003-08-13 2004-09-21 James V. Waldo, Jr. Heat-moisture exchanger with aerosol by-pass
EP1660004A4 (fr) 2003-08-18 2017-05-31 Breathe Technologies, Inc. Procede et dispositif pour ventilation non invasive avec interface nasale
WO2005079726A1 (fr) 2004-02-23 2005-09-01 Fisher & Paykel Healthcare Limited Appareil d'assistance respiratoire
EP1737524B1 (fr) 2004-04-02 2018-10-10 Fisher & Paykel Healthcare Limited Appareil d'assistance a la respiration
US7061252B2 (en) 2004-07-02 2006-06-13 Hudson Respiratory Care, Inc. Electrical arcing protection circuit
LT3766534T (lt) 2004-08-20 2022-10-25 Fisher & Paykel Healthcare Limited Prietaisas pacientui tiekiamų dujų savybėms matuoti
US7811253B2 (en) * 2004-12-09 2010-10-12 Applied Medical Resources Corporation Insufflation gas warmer and humidifier
US7680532B2 (en) * 2005-02-25 2010-03-16 Joseph Wiesel Detecting atrial fibrillation, method of and apparatus for
JP2009504278A (ja) 2005-08-15 2009-02-05 レスメド・リミテッド Ｃｐａｐ装置用加湿器槽
WO2007019628A1 (fr) 2005-08-15 2007-02-22 Resmed Ltd Ensemble generateur de flux de ventilation spontanee en pression positive continue et humidificateur a bas prix
US11497407B2 (en) * 2005-09-12 2022-11-15 ResMed Pty Ltd High flow therapy device utilizing a non-sealing respiratory interface and related methods
US11696992B2 (en) 2005-09-12 2023-07-11 ResMed Pty Ltd High flow therapy device utilizing a non-sealing respiratory interface and related methods
US11833301B2 (en) 2005-09-12 2023-12-05 ResMed Pty Ltd High flow therapy device utilizing a non-sealing respiratory interface and related methods
US11717174B2 (en) * 2005-09-12 2023-08-08 ResMed Pty Ltd High flow therapy device utilizing a non-sealing respiratory interface and related methods
US11458270B2 (en) 2005-09-12 2022-10-04 ResMed Pty Ltd High flow therapy device utilizing a non-sealing respiratory interface and related methods
US8522782B2 (en) * 2005-09-12 2013-09-03 Mergenet Medical, Inc. High flow therapy device utilizing a non-sealing respiratory interface and related methods
CA2623756A1 (fr) 2005-09-20 2007-03-29 Lutz Freitag Systemes, procedes et appareils destine a l'aide respiratoire d'un patient
WO2007142812A2 (fr) 2006-05-18 2007-12-13 Breathe Technologies, Inc. Espaceur de trachéostome, méthode de trachéotomie, et appareil pour insérer un espaceur de trachéostome
US8211052B1 (en) 2006-07-13 2012-07-03 Lexion Medical Llc Charged hydrator
DE202007019688U1 (de) 2006-07-14 2015-07-14 Fisher & Paykel Healthcare Ltd. Atemhilfsgerät
WO2008019102A2 (fr) 2006-08-03 2008-02-14 Breathe Technologies, Inc. Procédés et dispositifs de support respiratoire peu invasif
US11318267B2 (en) 2006-09-12 2022-05-03 ResMed Pty Ltd High flow therapy device utilizing a non-sealing respiratory interface and related methods
EP2079505B1 (fr) * 2006-11-08 2020-07-15 ResMed Pty Ltd Conduit destiné à être utilisé dans un appareil respiratoire
WO2008144589A1 (fr) 2007-05-18 2008-11-27 Breathe Technologies, Inc. Procédés et dispositifs pour détecter la respiration et fournir une thérapie de ventilation
US8365726B2 (en) 2007-06-07 2013-02-05 Resmed Limited Tub for humidifier
JP5513392B2 (ja) 2007-09-26 2014-06-04 ブリーズ・テクノロジーズ・インコーポレーテッド 睡眠時無呼吸を治療するための方法及び装置
CA2700878C (fr) 2007-09-26 2018-07-24 Breathe Technologies, Inc. Procedes et dispositifs permettant d'assister le flux d'inspiration et d'expiration dans une therapie par ventilation
US8905023B2 (en) 2007-10-05 2014-12-09 Vapotherm, Inc. Hyperthermic humidification system
US7983542B2 (en) * 2007-10-29 2011-07-19 Smiths Medical Asd, Inc. PID coefficient adjustment for respiratory heater closed loop control
US7777635B2 (en) * 2007-10-29 2010-08-17 Smiths Medical Asd, Inc. Power failure management for respiratory system heater unit
US9072848B2 (en) * 2007-11-05 2015-07-07 Resmed Limited Ventilation system and control thereof
AU2009219787B2 (en) * 2008-02-26 2014-05-29 Koninklijke Philips Electronics N.V. Pressure support system with upstream humidifier
US9802022B2 (en) * 2008-03-06 2017-10-31 Resmed Limited Humidification of respiratory gases
WO2009151791A2 (fr) 2008-04-18 2009-12-17 Breathe Technologies, Inc. Procédés et dispositifs pour détecter la respiration et réguler des fonctions respiratoires
US8770193B2 (en) 2008-04-18 2014-07-08 Breathe Technologies, Inc. Methods and devices for sensing respiration and controlling ventilator functions
DE102008022663B4 (de) 2008-05-07 2012-10-31 Schauenburg Hose Technology Gmbh Stretch-Schlauch
US9505164B2 (en) 2009-12-30 2016-11-29 Schauenburg Technology Se Tapered helically reinforced hose and its manufacture
US10258757B2 (en) 2008-05-12 2019-04-16 Fisher & Paykel Healthcare Limited Patient interface and aspects thereof
US10792451B2 (en) 2008-05-12 2020-10-06 Fisher & Paykel Healthcare Limited Patient interface and aspects thereof
DK2300088T3 (en) * 2008-05-27 2016-05-23 Fisher & Paykel Healthcare Ltd CONTROL OF THE TEMPERATURE IN A HUMIDIFICATION chamber for accurate humidity control
NZ727179A (en) 2008-06-05 2018-06-29 Resmed Ltd Treatment of respiratory conditions
US11660413B2 (en) 2008-07-18 2023-05-30 Fisher & Paykel Healthcare Limited Breathing assistance apparatus
US8677999B2 (en) 2008-08-22 2014-03-25 Breathe Technologies, Inc. Methods and devices for providing mechanical ventilation with an open airway interface
US9903371B2 (en) 2008-09-17 2018-02-27 Resmed Limited Cuff for air delivery conduit
US10252020B2 (en) 2008-10-01 2019-04-09 Breathe Technologies, Inc. Ventilator with biofeedback monitoring and control for improving patient activity and health
DK3323462T3 (da) 2008-10-10 2022-01-17 Fisher & Paykel Healthcare Ltd Næsepuder til en patientgrænseflade.
US9964238B2 (en) 2009-01-15 2018-05-08 Globalmed, Inc. Stretch hose and hose production method
US9132250B2 (en) 2009-09-03 2015-09-15 Breathe Technologies, Inc. Methods, systems and devices for non-invasive ventilation including a non-sealing ventilation interface with an entrainment port and/or pressure feature
US9962512B2 (en) 2009-04-02 2018-05-08 Breathe Technologies, Inc. Methods, systems and devices for non-invasive ventilation including a non-sealing ventilation interface with a free space nozzle feature
CA2757588C (fr) 2009-04-02 2017-01-03 Breathe Technologies, Inc. Procedes, systemes et dispositifs de ventilation ouverte non invasive a l'aide d'ajutages de fourniture de gaz a l'air libre
US8931481B2 (en) 2009-06-04 2015-01-13 Redmed Limited Flow generator chassis assembly with suspension seal
AU2010206053B2 (en) 2009-07-31 2014-08-07 ResMed Pty Ltd Wire Heated Tube with Temperature Control System, Tube Type Detection, and Active Over Temperature Protection for Humidifier for Respiratory Apparatus
USD742508S1 (en) 2013-07-12 2015-11-03 Resmed Limited Air delivery tube with cuff
CN102762250B (zh) 2009-09-03 2017-09-26 呼吸科技公司 用于包括具有夹带端口和/或压力特征的非密封通气界面的无创通气的方法、系统和装置
WO2011062510A1 (fr) 2009-11-18 2011-05-26 Fisher & Paykel Healthcare Limited Interface nasale
JP6017312B2 (ja) 2009-12-22 2016-10-26 フィッシャー アンド ペイケル ヘルスケア リミテッド 医療用回路用部品
EP3777937A1 (fr) * 2010-04-26 2021-02-17 VERO Biotech LLC Administration d'oxyde nitrique ultra pur (no)
CN102933247B (zh) * 2010-06-04 2016-04-20 皇家飞利浦电子股份有限公司 患者回路中温度的自动控制
AU2011292111B2 (en) 2010-08-16 2015-03-26 Breathe Technologies, Inc. Methods, systems and devices using LOX to provide ventilatory support
JP6097689B2 (ja) * 2010-09-06 2017-03-15 レスメド・リミテッドＲｅｓＭｅｄ Ｌｉｍｉｔｅｄ レインアウトを防ぐための方法および装置
WO2012045051A1 (fr) 2010-09-30 2012-04-05 Breathe Technologies, Inc. Procédés, systèmes et dispositifs d'humidification de voies respiratoires
EP2624903B1 (fr) 2010-10-08 2018-05-16 Fisher & Paykel Healthcare Limited Appareil d'assistance respiratoire
WO2012100291A1 (fr) 2011-01-24 2012-08-02 Resmed Limited Humidificateur
GB201102942D0 (en) * 2011-02-21 2011-04-06 Intersurgical Ag Improvements related to respiratory apparatus
US8511651B2 (en) 2011-03-29 2013-08-20 Smiths Medical Asd, Inc. Heater unit humidification chamber monitor
US10603456B2 (en) 2011-04-15 2020-03-31 Fisher & Paykel Healthcare Limited Interface comprising a nasal sealing portion
CA3219881A1 (fr) 2011-04-15 2012-10-18 Fisher & Paykel Healthcare Limited Interface comprenant une partie de pont nasal roulante
GB2557117B (en) 2011-06-03 2018-10-03 Fisher & Paykel Medical tubes and methods of manufacture
EP3984580A1 (fr) 2011-07-08 2022-04-20 ResMed Pty Ltd Coude pivotant et ensemble connecteur pour des systèmes d'interface de patient
JP2013087962A (ja) * 2011-10-13 2013-05-13 Panasonic Corp 加熱調理装置
US9987454B2 (en) * 2012-02-24 2018-06-05 Koninklijke Philips N.V. Rainout protection for respiratory therapy including humidification
GB2541550B (en) 2012-03-15 2017-06-21 Fisher & Paykel Healthcare Ltd Respiratory gas humidification system
WO2013147623A1 (fr) * 2012-03-30 2013-10-03 Dexter Chi Lun Cheung Système d'humidification
JP5873748B2 (ja) * 2012-04-05 2016-03-01 株式会社コロナ ミスト発生装置
GB2575894A (en) 2012-04-27 2020-01-29 Fisher & Paykel Healthcare Ltd Usability features for respiratory humidification system
US10080856B2 (en) 2012-08-08 2018-09-25 Fisher & Paykel Healthcare Limited Headgear for patient interface
EP4279106A3 (fr) 2012-09-04 2024-01-17 Fisher & Paykel Healthcare Limited Masque de valsalva
US9752790B2 (en) * 2012-09-21 2017-09-05 Great Innovations, LLC Convertible humidifier
US9863654B2 (en) * 2012-09-21 2018-01-09 Great Innovations, LLC Convertible dual tank humidifier
CN107361960B (zh) 2012-11-14 2020-11-06 费雪派克医疗保健有限公司 用于呼吸回路的分区加热
PL2928533T3 (pl) 2012-12-04 2021-05-17 Fisher & Paykel Healthcare Limited Rurki medyczne i sposoby ich wytwarzania
NZ743034A (en) 2013-02-01 2019-12-20 ResMed Pty Ltd Wire heated tube with temperature control system for humidifier for respiratory apparatus
CN108704213B (zh) * 2013-09-13 2021-06-22 费雪派克医疗保健有限公司 用于加湿系统的连接
GB2584026B (en) 2013-09-13 2021-03-17 Fisher & Paykel Healthcare Ltd A heater base for supplying humidified gases to a patient
WO2015060731A1 (fr) 2013-10-24 2015-04-30 Fisher & Paykel Healthcare Limited Administration de gaz respiratoires
CN103656830A (zh) * 2013-12-13 2014-03-26 科迈（常州）电子有限公司 一种家用呼吸机加湿器及其湿度控制方法
CA2934235C (fr) 2013-12-20 2023-02-28 Fisher & Paykel Healthcare Limited Raccordements de systeme d'humification
US10449319B2 (en) 2014-02-07 2019-10-22 Fisher & Paykel Healthcare Limited Respiratory humidification system
EP3501586B1 (fr) 2014-03-17 2021-02-17 Fisher & Paykel Healthcare Limited Tubes médicaux pour systèmes respiratoires
USD762843S1 (en) 2014-03-18 2016-08-02 Resmed Limited Air delivery tube
WO2015167347A1 (fr) 2014-05-02 2015-11-05 Fisher & Paykel Healthcare Limited Dispositif d'humidification de gaz
CN106535976B (zh) 2014-05-13 2019-04-05 费雪派克医疗保健有限公司 用于呼吸增湿系统的可用性特征
CN106535971B (zh) 2014-06-03 2020-12-04 费雪派克医疗保健有限公司 用于呼吸治疗系统的流动混合器
EP3185944A4 (fr) 2014-08-25 2018-04-04 Fisher&Paykel Healthcare Limited Masque respiratoire et parties, composants ou sous-ensembles associés
US11278689B2 (en) 2014-11-17 2022-03-22 Fisher & Paykel Healthcare Limited Humidification of respiratory gases
US20160158480A1 (en) * 2014-12-05 2016-06-09 Korea University Research And Business Foundation Tube for breath-inducing and apparatus for breath-inducing using the same
CN107206203B (zh) * 2014-12-09 2021-07-06 富利凯公司 用于在机械通气期间加热和加湿吸入气体的系统和方法
US10245406B2 (en) 2015-03-24 2019-04-02 Ventec Life Systems, Inc. Ventilator with integrated oxygen production
US11247015B2 (en) 2015-03-24 2022-02-15 Ventec Life Systems, Inc. Ventilator with integrated oxygen production
JP2018514301A (ja) 2015-04-27 2018-06-07 テレフレックス メディカル インコーポレイテッド 加湿デバイス
NZ739097A (en) * 2015-07-08 2022-02-25 Ventific Holdings Pty Ltd Device and system for heating respiratory conduit
TWI794733B (zh) 2015-09-09 2023-03-01 紐西蘭商費雪派克保健有限公司 呼吸加濕系統
USD807995S1 (en) 2015-09-22 2018-01-16 Fisher & Paykel Healthcare Limited Circuit kit for a humidifier
USD841147S1 (en) 2015-09-30 2019-02-19 Fisher & Paykel Healthcare Limited Circuit kit for a humidifier
EP3405246B1 (fr) * 2016-01-21 2023-08-09 Fisher & Paykel Healthcare Limited Système d'humidification de gaz médicaux
USD805630S1 (en) 2016-02-02 2017-12-19 Resmed Limited Air delivery tube
US10773049B2 (en) 2016-06-21 2020-09-15 Ventec Life Systems, Inc. Cough-assist systems with humidifier bypass
US10773037B2 (en) * 2016-06-23 2020-09-15 Loewenstein Medical Technology S.A. Ventilator and method
RU173397U1 (ru) * 2016-09-08 2017-08-24 Волкаст Лимитед Увлажнитель воздуха с дыхательным тренажером
WO2018081272A1 (fr) 2016-10-26 2018-05-03 Teleflex Medical Incorporated Système et méthode d'humidification à la demande proche du patient
US11351332B2 (en) 2016-12-07 2022-06-07 Fisher & Paykel Healthcare Limited Sensing arrangements for medical devices
US11311695B2 (en) 2016-12-22 2022-04-26 Fisher & Paykel Healthcare Limited Medical tubes and methods of manufacture
US11052214B2 (en) 2017-01-30 2021-07-06 Globalmed, Inc. Heated respiratory hose wiring
USD823455S1 (en) 2017-02-23 2018-07-17 Fisher & Paykel Healthcare Limited Cushion assembly for breathing mask assembly
USD824020S1 (en) 2017-02-23 2018-07-24 Fisher & Paykel Healthcare Limited Cushion assembly for breathing mask assembly
USD823454S1 (en) 2017-02-23 2018-07-17 Fisher & Paykel Healthcare Limited Cushion assembly for breathing mask assembly
US10792449B2 (en) 2017-10-03 2020-10-06 Breathe Technologies, Inc. Patient interface with integrated jet pump
US11338105B2 (en) 2018-03-27 2022-05-24 Globalmed, Inc. Respiratory humidification device
JP2021524795A (ja) 2018-05-13 2021-09-16 サミール・サレハ・アフマド ポータブル酸素濃縮器を使用するポータブル医療用人工呼吸器システム
USD937411S1 (en) 2019-08-30 2021-11-30 Fisher & Paykel Healthcare Limited Unit end connector

Family Cites Families (14)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3282266A (en) * 1962-08-02 1966-11-01 Jr John M Walker Method and apparatus for humidifying inhalation mixtures
US3434471A (en) * 1966-04-06 1969-03-25 Smithkline Corp Therapeutic intermittent positive pressure respirator
US3638926A (en) * 1967-09-27 1972-02-01 Alfred W Melville Humidification
US3659604A (en) * 1970-03-30 1972-05-02 Fisher & Paykel Humidifying means
GB1294809A (en) * 1971-08-23 1972-11-01 Philips Electronic Associated Gas humidifier for a medical respirator
US4060576A (en) * 1972-09-13 1977-11-29 Graham Cameron Grant Method and apparatus for vapor saturated gas delivery
US3864544A (en) * 1973-09-13 1975-02-04 Respiratory Care Electric heating unit for liquid
US4284878A (en) * 1979-08-20 1981-08-18 Bourns Medical Systems, Inc. Fluid level detector
US4305388A (en) * 1979-10-30 1981-12-15 Respiratory Care, Inc. Automatic inhalation temperature control
US4248217A (en) * 1979-10-30 1981-02-03 Respiratory Care, Inc. Inhalation heater control
GB2096468B (en) * 1981-04-03 1984-11-14 Yeda Res & Dev Improvement in or relating to an apparatus for medical treatment
US4430994A (en) * 1981-05-11 1984-02-14 Clawson Burrell E Respiratory gas heating and humidifying methods and apparatus
JPS58157471A (ja) * 1982-03-15 1983-09-19 株式会社東芝 吸入器
US4529867A (en) * 1984-02-09 1985-07-16 Inspiron Corporation Humidifier and heater

Non-Patent Citations (1)

* Cited by examiner, † Cited by third party
Title
See references of WO8602566A1 *

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US4621632A (en) 1986-11-11
DE3583862D1 (de) 1991-09-26
JPH0529468B2 (fr) 1993-04-30
CA1225303A (fr) 1987-08-11
EP0201529B1 (fr) 1991-08-21
WO1986002566A1 (fr) 1986-05-09
JPS62500702A (ja) 1987-03-26

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